Tissue sealing electrosurgery device and methods of sealing tissue

ABSTRACT

An electrosurgery medical device is enhanced with unique solution-assistance, and comprises, in combination, co-operating device jaws including jaw portions for manipulating tissue, and a plurality of solution infusion openings defined and spaced along each of the jaw portions, for receiving electrolytic solution and infusing the solution onto and into tissue to be manipulated, along said jaw portions. As preferred, the device further comprises at least one, and most preferably, many, longitudinal groove(s) along at least one and most preferably, both, of the jaw portions, with the solution infusion openings located in the groove or grooves. The solution is energized with RF energy and contributes to the functions and beneficial effects of the instrument. The solution exits the openings in the grooves at sufficient flow rates to separate substantially all the operative surfaces of the device from tissue, thereby substantially completely preventing adherence between the operative surfaces and tissue. The solution is further energized to a range of energy densities such that tissues to be affected are sealed against flow of blood, lymphatic fluids, air, and other bodily fluids and gases.

CROSS REFERENCE TO RELATED APPLICATIONS

The present application is a continuation of U.S. Ser. No. 09/580,229, filed May 26, 2000, which is a divisional of U.S. Ser. No. 08/901,890, filed Jul. 26, 1997, which application is hereby incorporated by reference, now U.S. Pat. No. 6,096,037.

BACKGROUND OF THE INVENTION

This invention relates to medical instruments, and more particularly to electrosurgical devices, and methods of manipulating tissue as, for example, by cutting the tissue.

DESCRIPTION OF THE RELATED ART

High-frequency alternating current was used to cut and coagulate human tissue as early as 1911. Current generators and electrode tipped instruments then progressed such that electrosurgical instruments and current generators are available in a multitude of configurations for both open procedures and endoscopic procedures, with microprocessor-controlled currents typically on the order of 500 KHz. Radiofrequency (RF) catheter ablation of brain lesions began in the 1960s, and RF ablation of heart tissue to control supraventricular tachyarrhythmias began in the 1980s. Thus, electrical energy, including but not limited to RF energy, is a known tool for a variety of effects on human tissue, including cutting, coagulating, and ablative necrosis, with and as a part of electrically conductive forceps. Bipolar and monopolar currents are both used with electrosurgical forceps. With monopolar current, a grounding pad is placed under the patient. A recent example of an electrically energized electrosurgical device is disclosed in U.S. Pat. No. 5,403,312 issued on Apr. 4, 1995 to Yates et al., and the disclosure is incorporated by reference.

SUMMARY OF THE INVENTION

An object of the present invention is to provide an electrosurgery tissue sealing medical device which may and also may not be a forceps.

Another object of the present invention is to provide an electrosurgery tissue sealing device such as a forceps that seals tissue by a unique flow of an electrolytic fluid or solution to the manipulating portions of the device in combination with energization of the solution with electrical energy. The effect of the solution and energy may be enhanced with pressure. The solution is brought into contact with and infuses the tissue. The solution may include saline as well as other non-toxic and toxic electrolytic solutions, and may be energized with RF electrical energy. The body of the device itself may or not be energized.

The solution provides at least in part the beneficial functions and effects of the instrument. As preferred, pressure on the tissue is applied, and most preferably the effect of pressure is optimized, as by applying pressure across the tissue to be effected that is substantially uniform.

Another object of the invention is to provide an electrosurgery medical device as described, and methods of sealing tissue, in which tissues are sealed against flow of fluids including air. With the invention, for example, lung tissue is aerostatically and hemostatically sealed, with the tissue adjacent the sealed tissue retaining blood and air.

Another object of the invention is to provide an electrosurgery medical device that may take the form of open surgery forceps of a variety of specific forms, or endoscopic forceps, also of a variety of forms.

A further object of the invention is to provide an electrosurgery medical device as described, in which the electrolytic solution by which the instrument functions is infused from the device onto and/or into the tissue along the operative portions of the device. With and without applied pressure, the solution coagulates and additionally seals tissue, as a result of being energized by RF energy, and also envelopes the operative portions of the device in solution all during manipulation of tissue, substantially completely preventing adherence between the instrument and tissue, substantially without flushing action.

In a principal aspect, then, the invention takes the form of an enhanced solution-assisted electrosurgery medical device comprising, in combination, cooperating device jaws including jaw portions for manipulating tissue, and a plurality of solution infusion openings defined and spaced along each of the jaw portions, for receiving solution and infusing solution onto and into the tissue along said jaw portions. While the device is contemplated with and without grooves, as preferred, the device further comprises at least one, and most preferably, many, longitudinal grooves along at least one and most preferably, both, of the jaw portions. Also most preferably, the solution infusion openings are located on the inside faces of the jaw portions, adjacent to and most preferably in the groove or grooves. The solution exiting the openings separates substantially all the operative surfaces of the device from tissue, substantially completely preventing adherence between the operative surfaces and tissue. The solution also aids in coagulation.

Coagulation aside, the invention causes hemostasis, aerostasis, and more generally, “omnistasis” of substantially any and all liquids and gases found in tissue being treated, such as lymphatic fluids and methane, as well as blood and air. These broader effects are understood to result from such actions as shrinkage of vascalature with and without coagulation, and without desiccation and carbonization.

Also as preferred, the operative portions of the device may take the form of a circular, semicircular or other regular and irregular geometric shape, to contain and/or isolate tissue to be affected and perhaps resected. As an example, with an enclosed geometric shape such as a circle, tissue surrounding lesions and/or tumors of the lung may be aerostatically and hemostatically sealed, resulting in an isolation of the lesions and/or tumors for resection. Lung function is retained. For adaption to unique tissue geometries, the operative portions of the device may be malleable, to be manipulated to substantially any needed contour. For procedures including resection, the device may include an advanceable and retractable blade, or additional functional structures and features.

These and other objects, advantages and features of the invention will become more apparent upon a reading of the detailed description of preferred embodiments of the invention, which follows, and reference to the drawing which accompanies this description.

BRIEF DESCRIPTION OF THE DRAWING

The accompanying drawing includes a variety of figures. Like numbers refer to like parts throughout the drawing. In the drawing:

FIG. 1 is a schematic diagram of the key elements of an electrical circuit according to the invention;

FIG. 2 is a perspective view of an endoscopic forceps according to the invention;

FIG. 3 is a detail view of a portion of the forceps of FIG. 2; and

FIG. 4 is a perspective view of a modification of the embodiment of FIG. 2;

FIG. 5 is a second modification, of the embodiment of FIG. 4, shown partially broken away;

FIG. 6 is a perspective view of an open surgery forceps according to the invention;

FIG. 7 is a detail view of a portion of the forceps of FIG. 6, partially broken away;

FIG. 8 is a schematic view of preferred saline supply equipment for the invention;

FIG. 9 is a perspective view of a portion of the jaws of an alternative device;

FIG. 10 is a perspective view similar to FIG. 9 of another alternative device;

FIG. 11 is a cross-sectional view along line 11—11 of FIG. 9; and

FIG. 12 is a perspective view of yet another alternative device.

DESCRIPTION OF THE PREFERRED ENDOWMENTS

Electrosurgery uses electrical energy to heat tissue and cause a variety of effects such as cutting, coagulation and ablative necrosis. The heat arises as the energy dissipates in the resistance of the tissue. The effect is dependent on both temperature and time. Lower temperatures for longer times often yield the same effect as higher temperatures for shorter times. Normal body temperature is approximately 37° C. No significant long-term effect is caused by temperatures in the range of 37° C. to 40° C. In the range of 41° C. to 44° C., cell damage is reversible for exposure times less than several hours. In the range of 45° C. to 49° C., cell damage becomes irreversible at increasingly short intervals. The following table states expected effects at higher temperatures:

Temperature (° C.) Effect 50-69 Irreversible cell damage - ablation necrosis.  70 Threshold temperature for shrinkage of tissue. (Some collagen hydrogen bonds break at 60-68; those with cross-linkages break at 75-80.) 70-99 Range of coagulation. Hemostasis due to shrinkage of blood vessels. 100 Water boils. 100-200 Desiccation as fluid is vaporized. Dependent on the length of time during which heat is applied, carbonization may occur, and at higher temperatures, occurs quickly.

This table is not intended as a statement of scientifically precise ranges above and below which no similar effects will be found, and instead, is intended as a statement of generally accepted values which provide approximations of the ranges of the stated effects. Limitation of the appended claims in accordance with this and the further details of this description is intended to the extent such details are incorporated in the claims, and not otherwise.

As a consequence of the foregoing effects, preferred “soft” coagulation occurs at temperatures slightly above 70° C. Heat denatures and shrinks tissues and blood vessels, thereby leading, as desired, to control of bleeding. Cells are generally not ruptured. “Soft” coagulation is generally assured with voltages below 200 peak Volts.

Sparks are avoided. “Forced” coagulation can be accomplished with bursts of electrical energy. Electric arcs are generated. Deeper coagulation is achieved, at the cost of some carbonization and an occasional cutting effect. Spray coagulation is also possible. Tissue cutting occurs by desiccation, when the concentration of electrical energy, also referred to here as energy density, is acute, and the temperature of tissue is raised above 100° C.

For both coagulation and cutting by electrical energy, a sine wave waveform is employed, with a frequency of about 500 kHz. For cutting, increasing voltage to as much as 600 peak Volts leads to higher spark intensity which results in deeper cuts. Frequencies above 300,000 Hz avoid stimulating nerve and muscle cells, and generally assure that the effect on tissue is substantially purely thermal.

In contrast with the RF energy tissue-cutting electrosurgery tools of the past, significant purposes of the present invention are to provide a mechanism of avoiding desiccation of tissue at the electrode/tissue interface and to achieve sealing of tissues. By “sealing,” the effects of hemostasis, or arresting of bleeding; “aerostasis,” or arresting of the passage of air; and closure of tissues such as blood vessels against larger-scale passage of blood, among other effects, are intended. More specifically, the effect of sealing at the cellular level is a primary focus, as is sealing at the vascular level.

Referring to FIG. 1, key elements of a preferred electrical circuit according to the invention include an electrosurgical unit 10, a switch 12, and electrodes 14, 16. An effect is created on tissue 18 of a body 20. One electrode such as electrode 14 acts as a positive or active electrode, while the other such as electrode 16 acts as a negative or return electrode. Current flows directly from one electrode to the other primarily through only the tissue, as shown by arrows 22, 24, 26, 28, 29. No pad is needed under the patient. This is a bipolar configuration.

Referring to FIG. 2, a forceps 30 according to the invention is an endoscopic forceps, and includes manual handles 32, 34, an elongated shaft 36, and jaws 38, 40. The handles 32, 34 pivot together and apart and through a suitable mechanism (not shown; present in the incorporated prior art) control the jaws 38, 40 to also pivot together and apart about a pivot connection 42. Referring to FIG. 3, each jaw 38, 40 is formed in two parts, hinged together. The jaw 38 includes a link portion 44 connected directly to the forceps shaft 36, and the jaw 40 includes a link portion 46 also connected directly to the forceps shaft 36. A jaw portion 48 hingedly fastened to the jaw link portion 44 completes the jaw 38; a jaw portion 50 hingedly fastened to the jaw link portion 46 completes the jaw 40.

As stated in the background of the invention, a wide variety of alternatives to the structure described and shown in FIG. 2 are possible. Prominent examples from those incorporated include the structures of U.S. Pat. No. 5,403,312 (Yates et al.) issued Apr. 4, 1995; U.S. Pat. No. 5,395,312 (Desai) issued Mar. 7, 1995; and U.S. Pat. No. 5,318,589 (Lichtman et al.) issued Jun. 7, 1994

Still referring to FIG. 3, a solution supply tube 52 supplies electrolytic solution to an electrode strip 47 along the jaw portion 48, as will be described. A solution supply tube 54 supplies electrolytic solution to a similar strip 49 along the jaw portion 50. A wire 56 electrically connects to the solution supply tube 52; a wire 58 electrically connects to the solution supply tube 54. All the supplies 52, 54, 56, 58, both solution and electrical, extend from the proximal or manual handle end of the shaft 36, and connect to solution and electrical sources.

Referring to FIG. 4, and in a second form of a jaw, designated 140, a jaw portion 150 similar to jaw portion 50 in FIG. 3, includes a longitudinal dimension in the direction of arrow 160. A plurality of longitudinal grooves 162 are spaced side-by-side across the inner face 164 of the jaw portion 150. The grooves 162 extend the full longitudinal length of the jaw portion 150. The same is true of a mirror image jaw portion, not shown. Both jaw portions are incorporated in a structure as in FIG. 3, and could be placed in substitution for jaw portions 48, 50 in FIG. 3. Grooves, not shown, also preferably extend along the corresponding jaw portions 48, 50 of FIGS. 2-3. Orientations of the grooves other than longitudinal are considered possible, within the limit of construction and arrangement to substantially retain solution along the operative jaw portions.

Bodily tissues to be manipulated have a natural surface roughness. This roughness significantly reduces the area of contact between the forceps jaws and manipulated tissues. Air gaps are created between conventional smooth-surfaced jaws and tissues. If the jaws were energized when dry, electrical resistance in the tissues would be increased, and the current density and tissue temperature would be extremely high. In practice, tissue surfaces are sometimes wet in spots, and yet tissue wetness is not controlled, such that electrical power is to be set on the assumption the inner jaw surfaces are dry. This assumption is necessary to minimize unwanted arcing, charring and smoke.

In contrast, in a forceps according to the invention, whether the jaw portions are grooved or smooth, whether the grooves are longitudinal or otherwise oriented, the jaw portions are uniquely formed of a material such as hollow stainless steel needle tubing such that solution infusion openings 166 may be and are formed in the jaw inner faces such as the inner face 164, as in FIG. 4. Further, the solution supplies 52, 54 shown by example in FIG. 3 may and do open into the openings 166, to supply solution to the openings 166. As most preferred, the openings 166 are laser drilled, and have a diameter in a range centered around four thousandths (0.004) of an inch, and most preferably in a range from two to six thousandths (0.002-0.006) inches.

The purpose of the openings 166 is to infuse solution onto and/or into the tissue adjacent to and otherwise in contact with the forceps jaw portions inner surfaces. It is understood the openings are appropriately as small in diameter as described above to assure more even flow among the openings than would otherwise occur. Further, the openings need not be so closely spaced as to mimic the surface roughness as tissues. Microporous surfaces are possibly acceptable, while they are also not necessary. Infusion of fluid through the jaws is to be maintained in a continuous flow during and throughout the application of RF energy in order for the desired tissue effect to be achieved.

With the described structure and similar structures and methods within the scope of the invention, numerous advantages are obtained. Deeper and quicker coagulation is possible. The conductive solution infused onto and into the tissues maintains relatively consistent maximal electrical contact areas, substantially preventing hot spots and allowing higher power than soft coagulation. Little to no arcing, cutting smoke or char is formed. Jaw and tissue surface temperatures are lower than otherwise, resulting in significantly less adhesion of tissue to jaw surfaces, and substantially no desiccation. One mode of coagulation may be used in the place of the three modes soft, forced, and spray. Coagulation is possible of even the most challenging oozing tissues such as lung, liver and spleen tissues. Coagulation is more precise, where other coagulation modes sometimes spark to the sides and produce coagulation where not desired.

Also, and importantly, electrosurgical cutting by desiccation may be avoided, and tissue sealing achieved. As desired, tissue sealing may occur alone, or be accompanied with mechanical cutting, as by a retractable and advancable blade as in U.S. Pat. No. 5,458,598, and as with blade 1210 in FIG. 12, or otherwise. The tissue sealing itself is understood to occur by flow of electrolytic solution to the manipulating portions of the forceps in combination with energization of the solution with electrical energy, and when included, in combination with pressure on, or compression of, the tissue. Compression of tissue is understood to deform tissues into conditions of sealing of tissues and especially vascalature. Compression of tissue followed by application of solution and energy is understood to permanently maintain compressed deformation of tissue, when present, and to shrink tissue and cause proteins to fix in place. Additional understanding of others is provided in the Yates et al. patent referenced above.

The body of the forceps itself may or not be energized. As most preferred, the solution primarily provides the beneficial functions and effects of the instrument. The effectiveness and extent of the tissue sealing is a unction primarily of the type of tissue being manipulated, the quantity of electrolytic solution supplied to the tissue, and the power of the electrical energy supplied to the solution. Tissues not previously considered to be suitable for manipulation, as by cutting, are rendered suitable for manipulation by being sealed against flow of fluids, including bodily fluids and air. With the invention, for example, lung tissue may be cut after sealing, with the tissue adjacent the sealed tissue retaining blood and air. Examples of the principal parameters of specific uses of the invention are provided in the following table. It is understood that the combined consequences of the parameters are that energy density in the tissue to be treated is in a range to effect sealing of the tissue. However, in general, a power output of 7 to 150 watts is preferred.

Fluid Quantity Power Tissue Effect 2 cc’s per minute 20 watts for 30 1 cm diameter hemostasis per electrode seconds vessel through the vessel 2 cc’s per minute 30 watts for 45 lung tissue hemostasis and per electrode seconds aerostasis 4 cc’s per minute 40 watts for 90 2 cm thickness hemostasis per electrode seconds liver tissue

In the examples for which the table is provided, the electrolytic solution is saline. In the first example, the device in use was a device as in FIG. 2, with electrodes of 16 gauge tubing, 1 cm long. The tool in use in the second and third examples was a forceps as in FIG. 6, with jaw portions 348, 350, to be described, 4 mm wide and 2.8 cm long. No desiccation was observed at the tissue/electrode interface. The device of FIG. 2 is preferred for vessel closure.

A wide variety of the currently installed electrosurgical generators could and will provide proper waveforms and power levels for driving the described forceps. The waveforms need only be sine waves at about 500 kHz, and the power need only be about 30 or more watts. As example of available generators, Valleylab generators are acceptable and widely available.

The electrolytic solution supplied to the forceps need only be saline, although a variety of non-toxic and toxic electrolytic solutions are possible. Toxic fluids may be desirable when excising undesired tissues, to prevent seeding during excision. Use of a pressure bulb is possible, as shown in FIG. 8. A flexible reservoir such as an intravenous (IV) bag 410 is surrounded with a more rigid rubber bulb 412 that is pressurized with air through an attached squeeze bulb 414. The reservoir is filled with solution through an injection port 416. An outflow line 418 has a filter 420 and a capillary tube flow restrictor 422 to meter flow. A clamp or valve 424 and connector 426 are also provided. A typical flow rate is one to two (1-2) cc/min at a maximum pressure of approximately sixteen pounds per square inch (16 psi)(52 mmHg). An example of opening diameters, numbers, and flow rate is as follows: opening diameter, 0.16 mm; number of openings, 13 per cm; and flow rate, 2 cc's per minute. A long slit has also been used and found acceptable. In this embodiment, flow rates of 0.01 to 50 cc/min are preferred.

It is understood that highly significant to the invention is the spacing of a plurality of solution openings along the jaw inner surfaces. Single openings as in Ohta et al., that effectively pour fluid adjacent one portion of forceps, are generally not considered suitable or effective. Openings along outer surfaces of the jaws, opposite inner surfaces, are also generally not considered suitable or effective.

Referring to FIGS. 4 and 5, the configurations of the most preferred solution openings are disclosed. Referring to FIG. 5, in a jaw 240, longitudinally spaced openings 166 are rotated from those shown in FIG. 4, in a jaw portion 250, to turn the openings away from most direct contact with tissues, and more carefully eliminate any unintended plugging of the openings. Electrical insulators 268 in the form of elongated strips extend alongside the tubes which include the openings 166.

Referring to FIG. 6, open surgical forceps 330 include jaws 338, 340 with jaw portions 348, 350. As with jaw portion 350 in FIG. 7, the jaw portions 348, 350 include spaced solution infusion openings 166 in the central longitudinal groove of a plurality of grooves 162. A central channel 370 of both jaw portions 348, 350, as shown relative to jaw portion 350 in FIG. 7, supplies solution to the openings 166 from solution supplies 52, 54. As with the endoscopic forceps of FIGS. 2-5, the open surgical forceps 330 benefits from the unique enhancement of electrosurgical functions through the infusion of electrolytic solutions onto and into tissues through the spaced, laser drilled, solution infusion openings in the grooves 162.

Referring to FIGS. 9 and 10, open surgical devices 430 and 530 also include jaws 438, 440 and 538, 540, respectively. The jaw portions of these devices are curved, and in the case of device 430, circular, to adapt the invention to specialized surgical situations of tissue manipulation, such as those in which fluid flow is to be terminated all around a tissue to be isolated and resected or excised. An example of such a tissue is a lesion or tumor of lung tissue. In endoscopic or open surgery, such lesions or tumors may be encircled and/or isolated, surrounding tissue sealed, and the lesions or tumors thereafter resected. Preferably, a one centimeter margin is resected about any lesion or tumor, with the lesion or tumor. As shown, the devices 430, 530 are formed of substantially square cross-section tubing, best shown in the cross-sectional drawing of FIG. 11. As most preferred, the tubing incorporates a central, depressed, cross-sectionally rectangular, and elongated groove 462 and equilaterally spaced, cross-sectionally triangular, parallel, and elongated outer grooves 464, 465.

Laser drilled openings 466, similar to openings 166 described above, are located in and spaced along the central groove 462.

Alternate cross-sectional shapes of tubing may be employed, as exemplified in FIG. 12. Flatter operative, e.g., inner faces of tubing are preferred within limits of constructing and arranging the operative faces to facilitate firm grasping and holding of tissue. Non-operative surfaces, being less of concern, may adapt to a variety of contours for a variety of alternate reasons. Further, malleable tubing may be employed, to permit the surgeon to shape the operative portions of the invented devices to specific physiological situations.

The infusion of conductive solutions, referred to here also as electrolytic solutions, simultaneously with the application of RF energy to tissues is discussed in further detail in U.S. Pat. No. 5,431,649 entitled “Method and Apparatus for R-F Ablation,” in the name of Peter M. J. Mulier and Michael F. Hoey; in U.S. Pat. No. 5,609,151, entitled “Method and Apparatus for R-F Ablation,” in the name of Peter M. J. Mulier. The foregoing patents are commonly assigned to the assignee of the present invention, and are incorporated by reference here.

The preferred embodiments, and the processes of making and using them, are now considered to be described in such fill, clear, concise and exact terms as to enable a person of skill in the art to make and use the same. Those skilled in the art will recognize that the preferred embodiments may be altered and modified without departing from the true spirit and scope of the invention as defined in the appended claims. For example, if the invented device is incorporated in forceps, the forceps may be varied in a range from excision and cutting biopsy forceps, to endoscopic forceps, dissecting forceps, and traumatic, atraumatic and flexible endoscopic grasping forceps. The jaws may close into full and tight contact with each other, or close into spaced relationship to each other, to accommodate tissue for purposes other than cutting. As expressed above, parallel spaced relationship is considered most preferably for uniformity of application of pressure across tissue to be affected.

A variety of features such as jaw serrations, single acting and double acting jaws, closing springs, ratchet locks, fingertip rotation rings, color coding and smoke aspiration may or may not be included with the features described in detail. Devices according to the invention may be constructed and arranged to grasp, hold, fix, cut, dissect, expose, remove, extract, retrieve, and otherwise manipulate and treat organs, tissues, tissue masses, and objects. Endoscopic forceps according to the invention may be designed to be used through a trocar. Bipolar and monopolar currents may both be used. With monopolar current, grounding pads may be placed under patients. The described grooves may be eliminated in favor of alternative grooves.

For purposes of the appended claims, the term “manipulate” includes the described functions of grasping, holding, fixing, cutting, dissecting, exposing, removing, extracting, retrieving, coagulating, ablating and otherwise manipulating or similarly treating organs, tissues, tissue masses, and objects. Also for purposes of the appended claims, the term “tissue” includes organs, tissues, tissue masses, and objects. Further for purposes of the appended claims, the term “electrical energy sufficient to affect tissue” includes electrical energy sufficient to raise tissue temperature to cause non-reversible effect on tissue as described above.

To particularly point out and distinctly claim the subject matter regarded as invention, the following claims conclude this specification. 

We claim:
 1. An electrosurgical device for ablating tissue, the device comprising: a jaw comprising a first jaw arm and a second jaw arm, the first and second jaw arms each having a portion on an inner face for engaging tissue; a curved portion on at least one of the first jaw arm and the second jaw arm, the curved portion permitting at least one of the portions for engaging tissue to correspond to the contour of the tissue to be ablated; a plurality of infusion openings positioned along an inner face of at least one of the first and second jaw arms, the plurality of infusion openings in fluid communication with a source of an electrically conductive liquid; and an electrical conductor for conducting electrical energy to at least one of the first and second jaw arms.
 2. An electrosurgical device as in claim 1 wherein the infusion openings are positioned along the one or more hollow tubes.
 3. An electrosurgical device as in claim 1 wherein the infusion openings are micropores.
 4. An electrosurgical device as in claim 1 wherein the infusion openings have diameters in a range from about 0.002 to about 0.006 inches.
 5. An electrosurgical device as in claim 2 wherein the one or more hollow tubes comprise a conductive material.
 6. An elecrosurgical device as in claim 5 wherein the conductive material is metal.
 7. An electrosurgical device as in claim 6 wherein the metal is stainless steel.
 8. An electrosurgical device as in claim 1 wherein at least one of the portions for engaging tissue comprises an electrically insulated portion.
 9. An electrosurgical device as in claim 1 herein at least one of the portions for engaging tissue includes one or more grooves.
 10. An electrosurgical device as in claim 2 wherein the one or more hollow tubes are positioned within one or more grooves on at least one of the tissue engaging portions.
 11. An electrosurgical device as in claim 10 wherein the infusion openings are positioned along the one or more hollow tubes.
 12. An electrosurgical device as in claim 1 wherein the infusion openings are micropores.
 13. An electrosurgical device as in claim 1 wherein the infusion openings have diameters in a range from about 0.002 to about 0.006 inches.
 14. An electrosurgical device as in claim 1 further comprising a handle and a mechanism connected to the handle and to the first and second jaw arms, whereby the movement of the first jaw arm in relationship to the second jaw arm may be manipulated from the handle.
 15. An electrosurgical device as in claim 14 further comprising a shaft extending from the handle to the first and second jaw arms, the shaft and jaws arms being elongated to permit endoscopic use of the device.
 16. An electrosurgical device as in claim 1 further comprising a pivot for pivoting movement of the first and second jaw arms towards each other and away from each other.
 17. An electrosurgical device as in claim 1 further comprising means for moving the first and second jaw arms in a parallel spaced relationship.
 18. An electrosurgical device as in claim 1 further comprising means for substantially uniformly compressing tissue by the portions for engaging tissue.
 19. An electrosurgical device as in claim 1 wherein both of the portions for engaging tissue are curved to correspond to a contour of the tissue to be ablated.
 20. An electrosurgical device as in claim 1 wherein the curved portion has a circular contour.
 21. An electrosurgical device as in claim 1 wherein at least one portion for engaging tissue comprises a porous surface.
 22. An electrosurgical system for ablating tissue, the system comprising: a forceps, the forceps having a first jaw arm and a second jaw arm, each jaw arm including a plurality of infusion openings and at least one electrical conductor; the forceps having a curved portion on each of the first jaw arm and the second jaw arm, the curved portion permitting at least one of the first jaw arm and second jaw arm to correspond to the contour of the tissue to be ablated; an electrically conductive liquid source in fluid communication with the plurality of openings; and an electrical energy source for supplying electrical energy to the electrical conductor.
 23. An electrosurgical system as in claim 22 wherein each jaw arm includes a hollow tube in fluid communication with the plurality of infusion openings and the electrically conductive liquid source.
 24. An electrosurgical system as in claim 23 wherein the infusion openings are positioned along the hollow tube.
 25. An electrosurgical system as in claim 22 wherein the infusion openings are micropores.
 26. An electrosurgical system as in claim 22 wherein the infusion openings have diameters in a range from about 0.002 to about 0.006 inches.
 27. An electrosurgical system as in claim 22 wherein the hollow tube comprises metal.
 28. An electrosurgical system as in claim 27 wherein the hollow tube comprises stainless steel.
 29. An electrosurgical system as in claim 22 wherein the electrically conductive liquid is saline solution.
 30. An electrosurgical system as in claim 22 wherein the electrically conductive liquid source supplies electrically conductive liquid at a rate in a range of about 0.01 to about 100 cc/mm.
 31. An electrosurgical system as in claim 22 wherein the electrical energy source supplies electrical energy at a power in a range of about 1 to about 200 watts.
 32. An electrosurgical system as in claim 22 wherein the electrically conductive liquid source comprises a reservoir.
 33. An electrosurgical system as in claim 32 wherein the reservoir is an IV bag.
 34. An electrosurgical system as in claim 22 wherein the electrical energy source is a RF generator.
 35. An electrosurgical device as in claim 34 wherein the RF generator provides RF energy having a sine wave waveform.
 36. An electrosurgical device as in claim 35 wherein the sine wave waveform has a frequency of about 500 kHz.
 37. A method of ablating tissue using an electrosurgical system, the method comprising: providing an electrosurgical forceps, the forceps having a first jaw arm and a second jaw arm, each jaw arm including a plurality of infusion openings and at least one electrical conductor, the forceps having a curved portion on each of the first jaw arm and the second jaw arm, the curved portion permitting at least one of the first jaw arm and second jaw arm to correspond to the contour of the tissue to be ablated; grasping an area of tissue using the curved electrosurgical forceps; supplying an electrically conductive fluid from an electrically conductive solution source to the plurality of infusion openings; and supplying electrical energy from an electrical energy source to the electrical conductor.
 38. A method as in claim 37 wherein the supplied electrically conductive liquid is saline solution.
 39. A method as in claim 37 wherein the electrically conductive liquid is supplied at a rate in a range of about 0.01 to about 100 cc/mm.
 40. A method as in claim 37 wherein the electrical energy is supplied at a power in a range of about 1 to about 200 watts.
 41. A method as in claim 37 wherein the electrically conductive liquid is supplied from a reservoir.
 42. A method as in claim 37 wherein the reservoir is an IV bag.
 43. A method as in claim 37 wherein the electrically conductive liquid is supplied at a rate in a range of about 0.01 to about 100 cc/mm while the electrical energy is supplied at a power in a range of about 1 to about 200 watts.
 44. A method as in claim 43 wherein the electrically conductive liquid is supplied at a rate in a range of about 2 to 8 cc/mm while the electrical energy is supplied at a power in a range of about 20 to 40 watts.
 45. A method as in claim 37 wherein the electrical energy source is a RF generator.
 46. An electrosurgical device as in claim 45 wherein the RF generator provides RF energy having a sine wave waveform.
 47. An electrosurgical device as in claim 46 wherein the sine wave waveform has a frequency of about 500 kHz. 